US20200179623A1 - Testing method for a dry powder inhaler - Google Patents

Testing method for a dry powder inhaler Download PDF

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US20200179623A1
US20200179623A1 US16/477,380 US201816477380A US2020179623A1 US 20200179623 A1 US20200179623 A1 US 20200179623A1 US 201816477380 A US201816477380 A US 201816477380A US 2020179623 A1 US2020179623 A1 US 2020179623A1
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plume
inhaler
dry powder
cross
discharged
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Denis Henry O'SULLIVAN
Daniel R BUCK
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Norton Waterford Ltd
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Assigned to NORTON (WATERFORD) LIMITED reassignment NORTON (WATERFORD) LIMITED ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BUCK, DANIEL R., O'SULLIVAN, Denis Henry
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/0005—Details of inhalators; Constructional features thereof with means for agitating the medicament
    • A61M15/0006—Details of inhalators; Constructional features thereof with means for agitating the medicament using rotating means
    • A61M15/0008—Details of inhalators; Constructional features thereof with means for agitating the medicament using rotating means rotating by airflow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0065—Inhalators with dosage or measuring devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/13—Amines
    • A61K31/135—Amines having aromatic rings, e.g. ketamine, nortriptyline
    • A61K31/137—Arylalkylamines, e.g. amphetamine, epinephrine, salbutamol, ephedrine or methadone
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/56—Compounds containing cyclopenta[a]hydrophenanthrene ring systems; Derivatives thereof, e.g. steroids
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/56—Compounds containing cyclopenta[a]hydrophenanthrene ring systems; Derivatives thereof, e.g. steroids
    • A61K31/58—Compounds containing cyclopenta[a]hydrophenanthrene ring systems; Derivatives thereof, e.g. steroids containing heterocyclic rings, e.g. danazol, stanozolol, pancuronium or digitogenin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/007—Pulmonary tract; Aromatherapy
    • A61K9/0073—Sprays or powders for inhalation; Aerolised or nebulised preparations generated by other means than thermal energy
    • A61K9/0075—Sprays or powders for inhalation; Aerolised or nebulised preparations generated by other means than thermal energy for inhalation via a dry powder inhaler [DPI], e.g. comprising micronized drug mixed with lactose carrier particles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/002—Details of inhalators; Constructional features thereof with air flow regulating means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/0021—Mouthpieces therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0086—Inhalation chambers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0091—Inhalators mechanically breath-triggered
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/14—Preparation of respiratory gases or vapours by mixing different fluids, one of them being in a liquid phase
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P11/00—Drugs for disorders of the respiratory system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P11/00—Drugs for disorders of the respiratory system
    • A61P11/06—Antiasthmatics
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/06—Investigating concentration of particle suspensions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/06—Solids
    • A61M2202/064—Powder
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/06—Investigating concentration of particle suspensions
    • G01N15/075—Investigating concentration of particle suspensions by optical means
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N2015/0042—Investigating dispersion of solids
    • G01N2015/0046—Investigating dispersion of solids in gas, e.g. smoke

Definitions

  • This invention relates to a testing method for a dry powder inhaler (DPI).
  • DPI dry powder inhaler
  • Dry powder inhalers represent one class of inhaler used for delivering inhalable medicament formulations.
  • Other classes of inhalers include a pressurised metered dose inhalers (pMDI) and a nebuliser.
  • an inhalable formulation is to present the formulation in the form of an aerosol of particles having a particle size suitable for lung deposition, which is typically a mass median aerodynamic diameter (MMAD) of 1-5 microns.
  • MMAD mass median aerodynamic diameter
  • pMDIs and nebulisers are generally more efficient than dry powder formulations since approaches which use dry powders tend to suffer from the drawback that only a small portion of the powdered active ingredient is actually inhaled into the lungs.
  • DPIs have the benefit that the energy required for aerosolisation of the formulation comes from the patient's own inhalation. This helps to avoid problems of poor hand-breath coordination (asynchrony) commonly associated with conventional pMDIs (see M. L. Levy et al. Prim Care Respir J. 2013, 22, 406-11).
  • the geometry and dynamics of the discharged plume are a significant factor in assessing the overall performance and efficacy of any inhaler. It may in particular have a substantial impact on the efficiency of delivery of medicament to the user.
  • Impaction techniques e.g. an Anderson cascade impactor (ACI) or a next-generation impactor (NGI).
  • ACI Anderson cascade impactor
  • NTI next-generation impactor
  • ACI Anderson cascade impactor
  • NTI next-generation impactor
  • ACI Anderson cascade impactor
  • NTI next-generation impactor
  • These techniques are based on drawing sample laden air through a stacked series of impaction stages, each comprising a collection surface designed to collect particles of a certain threshold inertia on the surface, whilst allowing the remainder of the particles to travel on to successive stages via an opening.
  • the air is controlled to progressively accelerate as it travels through the different stages such that each collection surface is effectively selecting particles of ever decreasing inertia (i.e. mass).
  • This allows a distribution of particles having a given inertia to be assessed within a discharged plume.
  • this method is limited to analysis of the aerodynamic size of the particles within the plume and does not give an assessment of the geometric or
  • the present invention provides a method of testing a dry powder inhaler comprising the steps of:
  • a dry powder inhaler 20 containing a dry powder formulation; actuating the inhaler to discharge a dose of the dry powder formulation in the form of a dry powder plume ( 24 );
  • FIG. 1 schematically depicts an example testing method in accordance with the invention to obtain a longitudinal view of a discharged powder plume
  • FIG. 2 schematically depicts a further example testing method in accordance with the invention to obtain a cross-sectional view of a discharged powder plume
  • FIG. 3 schematically depicts the distal end of an airflow adaptor of an example inhaler tested in accordance with the present invention
  • FIG. 4 schematically depicts the proximal end of an airflow adaptor of an example inhaler tested in accordance with the invention
  • FIG. 5 schematically depicts a further view of the airflow adaptor of the example inhaler tested in accordance with the invention
  • FIG. 6 schematically depicts a deagglomerator including a swirl chamber bypass port of the example inhaler tested in accordance with the invention
  • FIG. 7 schematically depicts an isometric view of the example inhaler tested in accordance with the present invention.
  • FIG. 8 shows a cross-sectional view of the example inhaler tested in accordance with the invention.
  • FIGS. 9-12 show an image of a powder plume captured in accordance with the invention.
  • FIGS. 13-16 show an image of a cross-section of a powder plume captured in accordance with the invention.
  • the invention provides a method of testing an inhaler based on performing an optical analysis of a dry powder medicament plume discharged from the inhaler upon actuation. More particularly, embodiments of the invention comprise illuminating the dry powder plume with a source of electromagnetic radiation and capturing one or more images of a pattern of radiation reflected or diffracted by the illuminated plume. The images are subsequently processed to determine and/or analyse one or more geometric and/or dynamic characteristics of the plume.
  • Implementations of the invention allow for highly detailed information to be obtained on the discharge behaviour of the inhaler, informing for instance future improvements to the design or to the way in which the inhaler is to be used.
  • the invention thus provides a contribution to the more overarching technical aim of achieving improvements in inhaler design and fluid dynamical performance.
  • the invention is based on capturing images of a pattern of radiation reflected or diffracted by the illuminated plume.
  • Capturing an image of the reflection pattern may simply correspond with capturing an image of the illuminated plume.
  • Geometrical characteristics means characteristics pertaining to the shape or dimensions of the plume. Geometrical characteristics may include, but are not limited to, a length of the plume, a width of the plume, a cross-sectional area of the plume at a particular distance along its length and/or the cross-sectional area as a function of distance along the plume length, as well as powder density or concentration distribution across the plume volume.
  • Dynamical characteristics means characteristics pertaining to the dynamics or mechanics of the plume as a physical system. Dynamical is intended to be understood synonymously with dynamic. Dynamical characteristics may include, but are not limited to, an envelope velocity of the plume (i.e. a velocity of the plume, taken as a whole), a direction of movement of the plume, a dispersion rate of the plume, and particle velocities within the plume.
  • FIGS. 1 and 2 schematically depict execution of respective first and second example testing methods in accordance with the invention.
  • FIG. 1 shows execution of an example testing method configured for capturing and analysing characteristics of a discharged plume as viewed along a longitudinal axis 42 of the plume.
  • An example inhaler 20 is actuated to discharge from a mouthpiece 22 a dose of medicament in the form of a dry powder plume 24 .
  • the plume is schematically depicted in FIG. 1 by means of a triangle representing a general shape of an outer envelope of the plume.
  • Axis 42 represents a central axis of the outer envelope shape of the plume, indicating an axis of orientational alignment or directionality.
  • Outer envelope means the outer profile (i.e. outline) of the plume, taken as a whole.
  • the central axis defines a line of directionality of the plume in the sense of a direction in which the powder plume is, taken as a whole, moving.
  • the outer envelope shape of the discharged plume 24 has a central axis 42 defining an angular orientation of the discharged plume, and wherein the method comprises analysing said angular orientation of the plume.
  • the present invention also comprises analysing a cross-sectional area 44 of an outer envelope shape of the discharged plume 24 at a given distance from a source of discharge of the plume, and optionally wherein said source of the discharge is defined as a distal end of a mouthpiece 22 of the inhaler 20 .
  • a laser 28 Upon actuation of the inhaler 20 and discharge of the dry powder plume 24 , a laser 28 is controlled to direct a laser light output 32 (i.e. EM radiation) onto the discharged power plume 24 .
  • the laser light output is generated or optically processed so as to provide a spatially expansive or diverging beam (spatially extended in one or both dimensions orthogonal to a propagation direction) across the plume in the form of a sheet of light.
  • a spatially expansive or diverging beam spatially extended in one or both dimensions orthogonal to a propagation direction
  • the laser 28 may be a FireFLY laser.
  • the laser 28 may be a visible light laser or may be a non-visible light laser such as for instance an infrared laser, ultraviolet laser, X-ray laser, or gamma-ray laser.
  • the term should also be understood as covering masers.
  • a laser light source 28 is provided in the particular example of FIG. 1 , it is to be understood that in this or any other example, the light source may be replaced by any suitable source of electromagnetic radiation. This may comprise a source of visible light or may be a source of a different form of electromagnetic radiation, such as infrared, microwaves, ultraviolet, x-rays or gamma rays for instance. Accordingly, the term images is to be construed broadly, as encompassing images formed through illumination by radiation of any region of the electromagnetic spectrum.
  • a high speed camera 36 is controlled to capture a plurality of images in succession of the pattern of laser light reflected or diffracted by the illuminated plume.
  • the images are preferably captured as a plurality of images in series.
  • the camera 36 may be configured to capture images recurrently at a frequency of 500 Hz for example.
  • the images may be captured using high-speed photography techniques.
  • details on the dynamics of the plume can be derived, including for instance internal dynamics of the particles within the plume as well as the dynamics of the overall plume itself, e.g. velocity, acceleration, dispersion rate.
  • the images may be captured at regular intervals at an interval frequency of from 300 to 1,000 Hz
  • the images are captured at a frequency of at least 500 Hz. It has been found by the inventors that an image capture frequency of at least 500 Hz provides a particularly beneficial balance between high detail in the dynamical analysis while not placing overly high demand upon any computing resources required to process the images.
  • the camera 36 may be configured to capture diffraction patterns generated by illumination of the particles of the plume 24 by the laser light 32 .
  • the method may be a form of laser diffraction technique, wherein the pattern of diffraction generated by the plume is captured in an image and used to determine or analyse the geometrical and/or dynamic properties of the plume, including for instance density or concentration distribution.
  • Axis 40 illustrates a direction of focus of the camera 36 , for instance the axis extending normally with respect an imaging plane of the camera.
  • the axis of focus of the camera is oriented approximately perpendicularly with respect to the axis of orientation (central axis) 42 of the plume 24 .
  • any suitable form of image capture device may be used which for instance comprises one or more elements sensitive to the respective band of the electromagnetic spectrum used to illuminate the plume. This may be a non-high-speed camera or a different variety of photosensitive device for instance.
  • a device specifically configured for capturing diffraction patterns generated by laser illumination of the particles of the plume may also be used for instance.
  • the images are processed to thereby determine and analyse one or more geometric and/or dynamic characteristics of the examined dry powder plume 24 .
  • This analysis may be performed by dedicated analysis software executed on a suitable computer device. Alternatively a dedicated image processor may be used to process the images and output analysis results.
  • Processing of the images of the longitudinal view of the powder plume captured in the method of FIG. 1 may typically enable determination (for each image) of at least: the orientation of the plume central axis 42 (relative to a given reference axis, such as an axis of a portion of the inhaler 20 , or an absolute horizontal or vertical axis for instance), the angle of the cone defined by the plume outer envelope, the width of the plume at different points along its longitudinal length, and a length of the plume.
  • a given reference axis such as an axis of a portion of the inhaler 20 , or an absolute horizontal or vertical axis for instance
  • the central axis can be derived by finding a line which defines a median point across the width of the captured plume pattern.
  • the angle of the cone defined by the plume outer envelope (the angular extent of the cone) can be derived by finding the angular displacement between two lines defining the angular boundaries of the plume. These angular boundary lines might be chosen for instance so that a certain minimum percentage of the total plume area or captured volume is within the lines, e.g. 90%.
  • the plume width may be defined as a linear distance between these two boundary lines.
  • the method may comprise determining an angle of deviation of the central axis 42 of the discharged plume 24 with respect to an axis of orientation of the mouthpiece 22 , i.e. the axis extending parallel to an inner conduit defined by the outer walls of the mouthpiece.
  • the dry powder inhaler 20 preferably comprises a mouthpiece 22 , and wherein the method comprises determining an angle of deviation of said central axis 42 of an outer envelope of the discharged plume 24 with respect to an axis of orientation of the mouthpiece.
  • the processing of the images and generation of analysis data may be performed simultaneously with capturing of the images or alternatively may be performed subsequently.
  • Processing of the images to thus derive indications or measures of the geometrical or dynamical characteristic(s) can be performed using any suitable image analysis procedure.
  • This may be computer implemented, for instance by means of image analysis software executed on a computer.
  • it may according to further examples be implemented by a suitable image processor.
  • Oxford Lasers Envision Patternate software is one example of suitable software which may be used to extract plume geometry and dynamics information from the captured images.
  • the software can be purchased from Oxford Lasers.
  • the Oxford Lasers EnVision Patternate software enables extraction from captured images of at least the following characteristics: plume cone angle, plume width, plume height, spray pattern ellipticity, spray pattern size, and spray event duration.
  • the EnVision software performs characterisation on a single image or can combine a sequence of images of the plume to form a composite image and then measures the cone angle, direction, plume geometry and other user-definable parameters.
  • a further piece of software which may in accordance with examples be used to extract plume geometry and dynamics information from the captured images is Oxford Lasers VidPIV software. This software may be purchased from Oxford Lasers.
  • the Oxford Lasers VidPIV software permits extraction in particular of plume velocity information, and allows an average velocity of the plume to be derived, as well as a full velocity vector map of the plume over time.
  • the obtained set of consecutive images may be processed to form a computational fluid dynamical model of the plume. This may be used to provide highly detailed information on a range of aspects of the plume behaviour throughout the duration of the discharge process including for instance aspects of its geometry, density and mechanics at different moments in time, as well as how these properties change as a function of time.
  • the inhaler 20 may be actuated in a vacuum chamber or an air flow chamber. This may improve accuracy or detail of the obtained analyses of plume geometry or dynamics. By conducting the test in a vacuum, the plume is unaffected by environmental (fluid) conditions for example.
  • FIG. 2 shows execution of an example testing method of the invention, configured for capturing and analysing characteristics of a discharged plume 24 across a given cross-section 44 at a given distance from a source of discharge of the plume.
  • a test inhaler 20 is actuated to discharge a dose of medicament in the form of a dry powder plume 24 .
  • the plume is illustrated schematically by a triangle shape, representing an outer envelope shape of the plume.
  • Axis 42 represents a central axis of the envelope shape, and indicates a general angle of orientation of the plume 24 . All terms may be understood as defined above.
  • a laser 28 is controlled to direct a source of laser light 32 across at least a particular cross-sectional region 44 of the illuminated plume 24 at a given distance from a source of discharge of the plume (in this case a distal end of the mouthpiece 22 ).
  • the given distance may be selected in advance, typically 3 cm or 6 cm. In particular examples, the distance may be 3 cm. Testing at this distance is standard within the field of inhaler testing.
  • the light output 32 of the laser 28 may be generated or optically processed so as to provide an approximately planar sheet of light. This may be directed (as shown in FIG. 2 ) radially across the width of a particular cross-sectional region 44 of the plume 24 .
  • a high-speed camera 36 is controlled to capture a series of images in quick succession (for instance at a frequency of at least 500 Hz).
  • Axis 40 indicates a direction of focus of the camera 36 .
  • the imaging plane of the camera is aligned in parallel with the direction of orientation (as indicated by central axis 42 ) of the dry powder plume 24 . This enables the camera to capture the reflection or diffraction pattern cast by the particular cross-section 44 of the plume being illuminated by the laser 28 .
  • a high-speed camera is indicated for the particular example illustrated in FIG. 2 .
  • this is not essential, and in further examples any suitable image or light pattern capturing device may be used.
  • a device configured specifically for capturing diffraction patterns may for instance be used in accordance with one or more examples.
  • the images are processed to thereby determine and analyse one or more geometric and/or dynamical characteristics of the dry powder plume 24 .
  • This analysis may be performed by dedicated analysis software executed on a suitable computer device.
  • a dedicated image processor may be used to process the images and output analysis results. Suitable example software is described above.
  • Processing of the images of the cross-sectional view 44 of the powder plume 24 captured in the method of FIG. 2 may typically enable determination of (for each image) at least: a radius of the plume cross section in each angular direction, maximal and minimal dimensions of the plume cross-section, a total area of the cross-section, and a concentration (or density) distribution of the powder across the cross-section 44 .
  • the cross-sectional area of the plume may provide an indication of deagglomeration performance of the inhaler. For example, a smaller cross-section may typically indicate a greater average powder density within said cross-section 44 . Where there is a greater density of powder, there is typically a greater rate of inter-particle collisions which lead to break-up (i.e. deagglomeration) of agglomerations of the powder medicament. For best medical results, it is preferable that the powder contains a high percentage fine particle fraction. Hence, by analysing cross-sectional area, an indication of post-discharge deagglomeration performance is attainable.
  • the cross-sectional area may also be relevant for other reasons. For instance, a narrower cross-section may in particular cases be preferable for instance to provide more directional discharge of the powder into a user's airway. A wider or more dispersed plume may for instance be more prone to spreading into the user's throat or mouth.
  • the concentration distribution of the powder may provide information relevant to the medical efficiency of the device. For example, a greater concentration of particles at a more central region may indicate a more directionally focussed plume. For instance, a plume having a high central concentration may be less prone to substantial radial dispersion as it travels toward the user's airway.
  • a more centrally concentrated plume may exhibit greater deagglomeration action after discharge from the inhaler due to increased particle interactions.
  • Powder concentration distribution means powder density distribution across the given cross-section 44 .
  • the concentration distribution may be in the form of a set of values of powder density or concentration at different points across the imaged cross-section 44 .
  • the present invention comprises determining a powder concentration distribution across a given cross-section 44 of the discharged plume 24 at a given distance from a source of discharge of the plume.
  • a number of different cross-sections 44 may be imaged at different distances from the mouthpiece 22 , and in these cases, the processing of the images may enable determination of the above properties for each of the imaged cross-sections.
  • the processing of the images and generation of analysis data may be performed simultaneously with capturing of the images or alternatively may be performed subsequently.
  • Benefits of the testing method of the present invention in providing instructive analysis of the geometric and dynamic characteristics of the generated powder plume may become more apparent through examination of a particular example of its application.
  • the inhaler tested is a breath-actuated dry powder inhaler comprising an airflow adaptor, the airflow adaptor comprising: a first conduit having a proximal end and a distal end, wherein the proximal end allows fluid communication from a deagglomerator outlet port to the distal end of the conduit, and wherein the airflow adaptor further comprises at least one second conduit for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the conduit when a breath induced low pressure is applied to the distal end of the airflow adaptor.
  • the ratio of the sum of the cross-sectional areas of the at least one second conduit to the cross-sectional area of the first conduit is such that when a breath induced low pressure is applied to the distal end of the airflow adaptor from about 20% to about 50% of the resulting airflow is through the at least one second conduit.
  • the at least one second conduit of the airflow adaptor hence allows air to by-pass the deagglomerator, thereby altering the dynamics of the generated powder plume.
  • FIG. 3 shows a distal end of the airflow adaptor 100 .
  • the airflow adaptor comprises a conduit 101 with a first circumferential flange 106 .
  • the airflow adaptor also comprises means for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the conduit when a breath induced low pressure is applied to the distal end of the airflow adaptor.
  • the means for thus allowing air to flow independently of the conduit are in the form of four apertures 102 , 103 , 104 , 105 in the first circumferential flange 106 . In alternative embodiments there may be other numbers of apertures.
  • FIG. 4 shows a view of the proximal end 201 of the airflow adaptor 200 in a partially constructed state.
  • the airflow adaptor comprises a conduit 202 with a first circumferential flange 203 .
  • the conduit shown has a circular cross-section; however, it may have any cross-sectional shape.
  • the airflow adaptor also comprises means for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the conduit when a breath induced low pressure is applied to the distal end of the airflow adaptor.
  • the means are in the form of four apertures 204 , 205 , 206 (fourth not shown) in the first circumferential flange 203 . Other numbers of apertures may also be provided.
  • the airflow adaptor 200 shown in FIG. 4 further comprises a second circumferential flange 208 .
  • the second circumferential flange also comprises four apertures 210 , 211 , 212 (fourth not shown).
  • the proximal end 209 of the conduit 202 allows fluid communication from a deagglomerator outlet port to the distal end of the conduit.
  • the airflow adaptor 200 shown in FIG. 4 has a mating surface 214 for mating with the outlet port of a deagglomerator outlet port. Preferably, they mate such that, during use, air will not flow across the mating surface.
  • the outlet port and the airflow adaptor may be a unitary structure.
  • FIG. 5 shows a view of the proximal end 301 of the airflow adaptor 300 in a fully constructed state.
  • four second conduits 304 , 305 , 306 can be seen, running from the second circumferential flange 308 to the first circumferential flange 303 .
  • These provide means for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the conduit when a breath induced low pressure is applied to the distal end of the airflow adaptor
  • the airflow adaptor may be moulded from any suitable polymeric material, including for instance polypropylene and acrylonitrile butadiene styrene.
  • FIG. 6 shows a deagglomerator 500 coupled with the airflow adaptor 501 .
  • the deagglomerator 500 comprises: an airflow adaptor 501 providing fluid communication between the outlet port 530 and a region exterior to the deagglomerator; an inner wall 512 defining a swirl chamber 514 extending along an axis B from a first end 518 to a second end 520 ; a dry powder supply port 522 in the first end 518 of the swirl chamber 514 for providing fluid communication between a dry powder delivery passageway of an inhaler and the first end 518 of the swirl chamber 514 ; at least one inlet port 524 , 525 in the inner wall 512 of the swirl chamber 514 adjacent to the first end 518 of the swirl chamber 514 providing fluid communication between a region exterior to the deagglomerator and the first end 518 of the swirl chamber; an outlet port 530 providing fluid communication between the second end 520 and the airflow adaptor 501 ; and at least one swirl chamber bypass port 502 , 503 ,
  • the at least one swirl chamber by-pass port 502 , 503 , 504 , 505 allows air to flow (shown by arrows labelled 5 ) from a proximal end of the airflow adaptor to a distal end of the airflow adaptor 501 independently of the swirl-chamber 514 when a breath-induced low pressure is applied to the distal end of the airflow adaptor.
  • the breath induced low pressure at the distal end of the airflow adaptor 501 also causes air to flow into the swirl chamber 514 through the dry powder supply port 522 and the at least one inlet port 524 , 525 .
  • the combined airflow (arrow 4 ) leaves the airflow adaptor 501 through the conduit 507 (shown by arrow 6 ).
  • the at least one swirl chamber bypass port shown in FIG. 6 is in the form of four apertures 502 , 503 , 504 , 505 in a first circumferential flange 506 of a conduit 507 of the airflow adaptor 501 .
  • the airflow adaptor 501 shown in FIG. 6 further comprises an optional second circumferential flange 508 which also comprises four apertures 509 , 510 , 511 (fourth not shown). When present, in use, the apertures 509 , 510 , 511 (fourth not shown) in the second circumferential flange 508 also form part of the swirl chamber bypass port.
  • the airflow adaptor shown in FIG. 6 is the airflow adaptor shown in FIG. 5 .
  • the second conduits of FIG. 5 perform the function of swirl chamber bypass ports. Indeed any of the airflow adaptors described herein when combined with a deagglomerator as described above provide a swirl chamber bypass port.
  • the ratio of the sum of the cross-sectional areas of the at least one swirl chamber bypass ports to the cross-sectional area of outlet port is such that that when a breath induced low pressure is applied to the distal end of the airflow adaptor from about 20% to about 30% of the resulting airflow is directed through the at least one swirl chamber bypass port.
  • FIG. 7 shows the external appearance of the breath-actuated dry powder inhaler 600 tested.
  • the breath-actuated dry powder inhaler comprises an airflow adaptor 601 having a conduit 602 and four second conduits 603 , 604 , 605 , 606 .
  • the conduit 602 and the second conduits 603 , 604 , 605 , 606 have circular cross-sections.
  • FIG. 8 shows the breath-actuated dry powder inhaler 700 comprising the deagglomerator 701 and the airflow adaptor 702 .
  • the airflow adaptor 702 comprises a conduit 703 with a first circumferential flange 704 comprising four apertures (not shown).
  • the airflow adaptor further comprises a second circumferential flange 705 also comprising four apertures (not shown).
  • the apertures in the first and second circumferential flanges perform the function of swirl chamber bypass ports (by performing the function of the at least one second conduit(s)).
  • a breath-actuated low pressure at the distal end 706 of the airflow adaptor 702 causes air to flow through the apertures (not shown) in the first 704 and second 705 circumferential flanges.
  • the breath-actuated low pressure at the distal end 706 of the airflow adaptor 702 also causes air to entrain medicament and deliver it to the swirl chamber 707 via a supply port.
  • the above described inhaler (henceforth referred to as a ‘high-flow inhaler’) has been tested using an embodiment of the testing method of the present invention.
  • a second inhaler (henceforth referred to as a ‘standard inhaler’) was also tested, this being similar to the first except that the airflow adaptor does not comprise the four second conduits 603 , 604 , 605 , 606 acting as swirl chamber by-pass conduits. Accordingly, when a breath induced low pressure is applied to the distal end of this second inhaler's airflow adaptor, all of the resulting airflow is directed through the swirl chamber.
  • FIGS. 9 and 10 show plume pattern images captured for each of two sample standard inhalers (i.e. without the by-pass conduits) tested in accordance with the longitudinal view test illustrated in FIG. 1 .
  • Table 1 sets out a summary of the results achieved for these two tests.
  • the table details average values for an orientation of the discharged plume (i.e. orientation angle of a central axis of the plume) relative to the mouthpiece of the inhaler, as well as cone angle of the outer envelope shape of the plume and total length and width of the plume.
  • the mouthpiece in this case was oriented with its outflow aligned horizontally.
  • the results of the test reveal some surprising features of the discharged plume geometry.
  • the discharged plume is oriented with a downward incline.
  • the test would reveal that the plume was emitted approximately horizontally, with any drop being commensurate only for example with the effects of gravity.
  • the results reveal a significant declination of the plume alignment.
  • average angle of a central axis of the plume with respect to vertical was found to be 104.96° (where 90° would have indicated perfect horizontal alignment). There is hence a misalignment in this case of approximately 15°.
  • Such an angular misalignment may have tangible effects on the medical efficiency of the inhaler in delivering the powdered medicament. For example, a greater angle of deviation may lead to less efficient delivery of the medicament to a user's airway, for instance by allowing some of the powder to be misdirected to undesired areas such as the throat or mouth.
  • FIGS. 11 and 12 show plume pattern images captured for each of two example high-flow inhalers (i.e. with the by-pass conduits) and Table 2 below sets out a summary of the results achieved for these two tests. The same quantities were measured as in the above described tests for the standard inhalers and, again, the mouthpiece was oriented with its outflow aligned horizontally.
  • the angle of orientation of the plume for the high-flow inhaler is closer to horizontal.
  • the average angle of the central axis of the plume from vertical was found to be 97.73°, i.e. deviating only approximately 8° from perfect horizontal alignment. This hence represents a reduction of approximately 7° in the angle of deviation of the plume from horizontal compared with the standard inhaler.
  • a more focussed or less dispersed plume may have tangible effects on efficiency or performance of the inhaler, for instance enabling greater directionality of the plume, thereby allowing easier targeting of the powdered medicament directly toward the airway of the user, and potentially limiting misdirecting of the medicament into the throat or mouth.
  • a more focussed plume may also increase so-called post-discharge deagglomeration action, wherein a particle-particle collision rate within the plume after ejection from the inhaler is increased due to the greater plume density. This leads to further deagglomeration of the powder, which improves medical efficacy of the medicament once delivered.
  • FIGS. 13 and 14 show plume pattern images captured for each of two example standard inhalers (i.e. without the by-pass conduits) tested in accordance with the cross-sectional view test illustrated in FIG. 2 .
  • the images capture a cross-section of the discharged plume at a distance of 3 cm from the inhaler mouthpiece Table 3 below details the numerical results for these tests, in particular setting out average values for a range of dimensional characteristics of the particular cross-section imaged.
  • FIGS. 15 and 16 show plume pattern images captured for two example high-flow inhalers tested in accordance with the cross-sectional view test of FIG. 2 .
  • the images again correspond to cross-sections at a distance of 3 cm from the inhaler mouthpiece.
  • Table 4 below details the average numerical results for the two tests.
  • the average cross-sectional area for the high-flow inhalers is significantly less than the corresponding areas for the standard inhalers.
  • the average area for the high-flow inhaler plumes decreases to 4.51 cm 2 compared to an average value of 6.16 cm 2 for the standard inhaler.
  • This decrease in size of the cross-section is also reflected in the value for the length of longest diameter, which has an average value of 2.97 cm for the high-flow inhaler compared to 3.72 cm for the standard inhaler.
  • the smaller cross-sectional area for the high-flow inhaler may indicate a more concentrated or focussed plume. As noted above, this may also indicate a greater directionality of the plume, allowing for more efficient delivery of the powdered medicament to the user's airway, or may indicate increased post-discharge deagglomeration action.
  • the colour distribution shows that for the high-flow inhaler plume, there is a significantly elevated powder density (or concentration) within a central region of the plume cross-section compared to more extremal regions. This indicates a more centrally focussed or concentrated plume, with central regions comprising a greater concentration of powder than outer regions.
  • example testing methods of the present invention enable technically relevant information concerning characteristics of the discharged medicament plume to be obtained.
  • the results of this testing may furthermore be utilised in modifying or refining the design of an inhaler.
  • results for two designs it may be seen that a particular distinguishing feature or modification of one design leads to an advantageous effect upon the geometric or dynamical characteristics of the plume.
  • results may then be utilised in further design procedures to improve the design.
  • the present invention also provides a method of designing a dry powder inhaler 20 , the inhaler being operable to discharge a dose of medicament in the form of a dry powder plume, the method comprising:
  • the method may comprises adjusting the design so as to minimise an angle of deviation of a central axis 42 of an outer envelope shape of the discharged plume 24 with respect to an axis of orientation of a mouthpiece 22 of the inhaler, and optionally wherein the mouthpiece defines a source of discharge of the plume.
  • the mouthpiece may define a source of discharge of the plume.
  • a large angle of deviation may be medically disadvantageous, leading to delivery of the powder to regions where it is not required, such as the throat or mouth. By minimising this angle, such deficiencies in the performance of the device may be ameliorated.
  • the method may comprise adjusting the design so as to reduce a cross-sectional area 44 of an outer envelope shape of the discharged plume 24 at a given distance from a source of discharge of the plume.
  • reducing the cross-section may increase deagglomeration action within the plume as it exits from the inhaler. This leads to finer breakdown of the powder and improved medical efficacy. Reducing the cross-section may also enable greater directionality in the projected plume, allowing for more focussed delivery of the power directly into the airway of the user.
  • the method may, additionally or alternatively, comprise adjusting the design so as to alter a concentration distribution of the powder across a given cross-section of the plume, the cross-section being located at a given distance from a source of discharge of the plume.
  • the design may be adjusted so as to increase a concentration of the powder within a central region of the cross section, proximal to a central point or centroid of the cross section.
  • increased concentration within a central region may improve medical efficacy, for example by rendering a more directionally focussed plume, or by increasing post-discharge deagglomeration action within the plume.
  • example test results presented above in respect of the standard and high-flow inhalers might be utilised in example design methods to refine a design of an inhaler in accordance with the distinguishing features of the high-flow inhaler which were found to lead to advantageous alterations in the characteristics of the inhaler plume.
  • a method of designing a dry powder inhaler wherein the dry powder inhaler is a breath-actuated dry powder inhaler comprising an airflow adaptor, the airflow adaptor comprising:
  • a first conduit having a proximal end and a distal end, wherein the proximal end allows fluid communication from a deagglomerator outlet port to the distal end of the first conduit, and
  • At least one second conduit for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the first conduit when a breath induced low pressure is applied to the distal end of the airflow adaptor
  • adjusting the design by adjusting a ratio of the sum of the cross-sectional areas of the at least one second conduit to the cross-sectional area of the first conduit to thereby alter one or more geometrical and/or dynamic characteristics of the dry powder plume discharged from the inhaler upon application of a breath induced low pressure to the distal end of the airflow adaptor.
  • the at least one second conduit changes the fluid dynamical properties of the consequently generated powder plume.
  • the extent of this adjustment depends upon the number of second conduits provided and also their cross-sectional areas.
  • the magnitude of the adjustment to the plume characteristics may be varied by altering the ratio of the aggregate cross-sectional areas of the at least one second conduit to the cross-sectional area of the first conduit. By varying this design feature, the characteristic of the plume can be tuned.
  • the first dry powder inhaler 20 is a breath-actuated dry powder inhaler comprising an airflow adaptor 100 , 200 , 300 , 50 , 702 , the airflow adaptor comprising:
  • a first conduit 101 , 202 , 302 having a proximal end and a distal end, wherein the proximal end allows fluid communication from a deagglomerator outlet port to the distal end of the first conduit, and
  • At least one second conduit 304 , 305 , 306 for allowing air to flow from a proximal end of the adaptor to a distal end of the adaptor independently of the airflow in the first conduit 101 , 202 , 302 when a breath induced low pressure is applied to the distal end of the airflow adaptor,
  • the method comprises adjusting a ratio of the sum of the cross-sectional areas of the at least one second conduit 304 , 305 , 306 to the cross-sectional area of the first conduit 101 , 202 , 302 so as to adjust vary one or more geometrical or dynamic characteristics of the dry powder plume discharged from the inhaler 20 upon application of a breath induced low pressure to the distal end of the airflow adaptor.
  • the present invention also provides a dry powder plume 24 generated by discharge from a dry powder inhaler 20 , characterised in that:
  • an angle of deviation of a central axis 42 of an outer envelope shape of the discharged plume 24 with respect to an axis of orientation of a mouthpiece 22 of the inhaler is no greater than 8 degrees, and a cross-sectional area 44 of an outer envelope shape of the discharged plume 24 at a distance of 3 cm from a source of discharge of the plume is no greater than 5 cm 2 .

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HUE061264T2 (hu) 2023-09-28
EP3884977B1 (fr) 2024-07-17
AU2018207234B2 (en) 2023-11-02
ES2936861T3 (es) 2023-03-22

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